WO2004002191A1 - Transducteur pour signaux bioacoustiques - Google Patents

Transducteur pour signaux bioacoustiques Download PDF

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Publication number
WO2004002191A1
WO2004002191A1 PCT/DK2003/000427 DK0300427W WO2004002191A1 WO 2004002191 A1 WO2004002191 A1 WO 2004002191A1 DK 0300427 W DK0300427 W DK 0300427W WO 2004002191 A1 WO2004002191 A1 WO 2004002191A1
Authority
WO
WIPO (PCT)
Prior art keywords
transducer
diaphragm
transducer according
housing
area
Prior art date
Application number
PCT/DK2003/000427
Other languages
English (en)
Inventor
Knud Bjørn ANDERSEN
Original Assignee
Bang & Olufsen Medicom A/S
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Bang & Olufsen Medicom A/S filed Critical Bang & Olufsen Medicom A/S
Priority to KR1020047020742A priority Critical patent/KR100991649B1/ko
Priority to JP2004514592A priority patent/JP4378280B2/ja
Priority to US10/518,588 priority patent/US7593534B2/en
Priority to EP03732253A priority patent/EP1552718B1/fr
Priority to AT03732253T priority patent/ATE551844T1/de
Priority to AU2003239776A priority patent/AU2003239776A1/en
Publication of WO2004002191A1 publication Critical patent/WO2004002191A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B7/00—Instruments for auscultation
    • A61B7/02—Stethoscopes
    • A61B7/04—Electric stethoscopes
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/46—Special adaptations for use as contact microphones, e.g. on musical instrument, on stethoscope
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0204—Acoustic sensors

Definitions

  • the invention concerns a transducer for bioacoustic signals comprising a transducer element having a front side and a rear side, the front side of which may establish an intimate contact with the surface of a body part, said surface being the transmitter of direct interior sound from the body, said transducer element being mounted in a housing subject to airborne noise, and having a surface surrounding the front side of said transducing element, said element and said surrounding surface being in intimate contact with the surface of said body part during use.
  • Transducers for bioacoustic signals emanating from a body usually belong to two main types applied to an outside surface of the body.
  • One type is a microphone in principle, in which the vibration of a delimited area of skin is picked up as pressure variations in the air surrounding the area of skin, usually the pressure variations in a closed volume delimited by the skin, the microphone diaphragm, and the housing.
  • An enclosed volume is essential to obtain a good low frequency response as well as protection from extraneous airborne noise - one early example is the standard binaural stethoscope in which the bell defines the volume.
  • the second type is an accelerometer in principle, in which a light-weight housing rests against the part of the body and the inertial mass inside provides reference in the generation of signals proportional to the instant acceleration.
  • US 6,028,942 relates to the chestpiece of an acoustic, non-amplified stethoscope having noise balancing means, in that a resonator is coupled to the reverse side of the diaphragm.
  • An embodiment using amplification is also shown. The purpose is to compensate the noise that is radiated into the tissue surrounding the front end when applied to the skin and which is added to the desired signal.
  • There is an air space between the tissue and the diaphragm that provides the output signal however this remarkably reduces the usefulness of the device in practice. It is probable that the elaborate equivalent circuits used in US 6,028,942 are misleading, because they do not take into account the pickup of airborne noise via the transducer housing mass itself.
  • the invention is based on a recognition that there is indeed a significant pickup of airborne noise by the housing of the transducer, and that the ensuing vibration of the housing acts on the diaphragm by pressing against the outer surface of the body. If the reverse side of the diaphragm picks up the extraneous airborne noise in a suitable phase relationship, the influence of the airborne noise, will be effectively eliminated in a frequency interval of interest.
  • the proper phase relationship may be available in a very narrow frequency range by just providing access for airborne noise to the rear side of the diaphragm, but further improvement in a frequency interval of interest may be obtained by suitable acoustical loading of the rear side of the diaphragm.
  • the invention is particular in that the effective area of the transducing element is less than 50% of the area of the surrounding surface of the housing and in that the rear side of the transducing element is loaded by an acoustical network which is in communication with the surrounding air, said loading creating an extinguishing relationship between airborne noise signals influencing the front and rear sides of the transducing element respectively.
  • the invention takes account of the fact that there are several paths of both the desired physiological signals and the offending airborne noises, and that influencing the housing also causes an influence on the transducing element.
  • an advantageous embodiment of the invention is particular in that the effective area of the transducing element is between 1/2 and 1/1000 of the area of the surrounding surface of the housing. It has been determined that there is an improvement in performance when the respective areas are held within these proportions.
  • the effect may be related to the area of contact to the skin and the density of the underlying tissue.
  • effective area is meant the area of the diaphragm that is actually flexing and contributing to the output, i.e. it is usually less than the opening in the surrounding surface.
  • this ratio is within the interval 0,2 > ad/ah > 0,05.
  • the transducing element is a compound diaphragm giving an electrical output when exposed to bending.
  • This may be obtained in the form of what has been termed a piezoelectric transflexural diaphragm, which is in fact a very thin piezoelectric layer, one side of which is usually bonded to a metal diaphragm and which has a metal layer deposited on the other side.
  • This laminate reacts to shear stresses in the piezoelectric layer occuring when the diaphragm is bent inwards and outwards by generating a voltage difference between the metal diaphragm and the metal deposit.
  • a further advantageous embodiment is particular in that the transducing element is a compound diaphragm giving an electrical output when exposed to differential stretching of the front side with respect to the rear side of the diaphragm.
  • the transducing element is a compound diaphragm giving an electrical output when exposed to differential stretching of the front side with respect to the rear side of the diaphragm.
  • a further advantageous embodiment is particular in that the acoustical network consists of a cavity in the housing being indirectly influenced by airborne noise.
  • a further advantageous embodiment is particular in that the acoustical network consists of a cavity and at least one port in the housing. This is in fact an enclosure for the diaphragm with a leak, and by suitably placing the resonant frequency of this cavity volume and port combination, an extension of the frequency response and in particular of the range of noise suppression may be obtained.
  • a further advantageous embodiment is particular in that the acoustical network consists of a cylindrical conduit having essentially the same diameter as the diaphragm. This corresponds to letting the diaphragm sit in the bottom of a well, which provides a good shielding and mechanical protection of the diaphragm and connections and reducing the risk that the closure of a port will change the frequency response of the transducer.
  • a further advantageous embodiment is particular in that the port is constituted by a narrow slit. This has the particular advantage that it is difficult accidentally to cover the whole length of the slit, which reduces the risk that the port will change its properties materially during practical use.
  • a further embodiment provides a non- wettable material for the slit surround.
  • An advantageous embodiment of the invention is particular in that an elastic material capable of transmitting mechanical vibration is provided in sealing relationship between the skin and the diaphragm.
  • the diaphragm may be made of stainless steel which is generally regarded as inert with respect to skin, there may be cases of nickel allergy, and for this reason and for normal surface protection of the diaphragm it may be desirable to provide the transducer with a layer of an elastomer.
  • the skilled person will be able to select a material which has suitable transmission properties for this application.
  • a further advantageous embodiment is particular in that the acoustical network means comprises damping material.
  • a further advantageous embodiment is particular in that the cylindrical conduit is provided with a damping material.
  • a further advantageous embodiment is particular in that damping material is used as a resistive element in a port.
  • a further advantageous embodiment is particular in that the damping material has water-repellent qualities.
  • the invention will be further described with reference to the drawing, in which three transducers are described, the first (Type I) having an enclosed space in contact with the rear of the diaphragm and only in indirect contact with the surrounding air, the second (Type II) having an opening leading to the rear of the diaphragm as the most primitive case of an acoustical network directly connected to the surrounding air that will function according to the invention, and the third (Type III) having a closed volume with a port as a further but more sophisticated case of an acoustical network that will function according to the invention.
  • Each transducer is documented by figures showing its equivalent diagram and figures showing the results obtained by simulation based on the dimensions of a useful transducer and the forces created during its practical use. Note that the absolute levels of the curves expressed in dB have no physical meaning as such, as the sound sources in the various situations have been normalised to unity.
  • the content of the figures is as follows:
  • Fig. 1 shows a transducer according to prior art placed on the skin of a body
  • Fig. la shows the construction of a prior art transducer
  • Fig. 2 identifies the components of a transducer according to a first embodiment of the invention (Type I),
  • Fig. 3 shows an electrical equivalent circuit of the transducer shown i Fig. 2,
  • Fig. 4 shows the S/N performance of a transducer shown in Fig. 2,
  • Fig. 5 identifies the components of a transducer according to a second embodiment of the invention (Type II),
  • Fig. 6 shows the S/N performance of a transducer shown in Fig. 7,
  • Fig. 7 shows the construction of a transducer according to a third embodiment of the invention (Type III)
  • Fig. 8 shows an electrical equivalent circuit of the transducer shown i Fig. 7,
  • Fig. 9 identifies the components of the transducer shown in Fig. 7,
  • Fig. 10 shows the S/N ratio performance of the Type III transducer
  • Fig. 11 shows results of changes of area ratio according to one aspect of the invention, changing the area of the housing
  • Fig. 12 shows results of changes of area ratio according to one aspect of the invention, changing the area of the diaphragm, and
  • Fig. 13 shows an equivalent circuit for determining the sensitivity to the desired physiological signals.
  • Sh Effective application area towards tissue of inactive transducer housing e.g. calculated from the housing radius ah and the sensor diaphragm radius ad for concentrically distributed area elements
  • Vp Air-chamber volume
  • Fig. 1 is seen a section of a body resting on its back with a transducer T placed against the skin.
  • the transducer shown in Fig. la consists of an outer housing 4 comprising an inner housing 3 holding a diaphragm 1 by its rim and creating a surround 5. Furthermore there is a clamping arrangement 6 for the signal lead and its electrostatic shielding.
  • the housing may also hold a pre-amplifier and impedance converter 2, e.g. using a phantom power supply.
  • the diaphragm 1 may be a transflexural piezoelectric laminate known per se which gives off a voltage when flexed or a piezoelectric element P.
  • One electrode consists of the actual metallic diaphragm, and the other is deposited onto the other side of the thin sheet of piezoelectric material.
  • the diaphragm is mounted flush with or at least in the same plane as the surrounding part of the housing, and the surround 5 has a diameter or width such that airtight contact with the skin ensured.
  • the housing is closed, thereby shielding the rear side of the diaphragm from airborne sound and creating a cavity C, which is a general representation of the prior art.
  • Fig. 2 is seen a simplified layout of the components in a transducer according to the invention
  • Fig. 3 is shown the electrical equivalent circuit of the transmission path from ambient noise via the transducer housing and to the front side of the sensor diaphragm (the side in touch with the body).
  • Ambient noise is introduced to the front side of the sensor diaphragm (facing the tissue) as the ambient noise pressure signal pushes on the transducer housing, thereby causing compression (pressure) in the underlying tissue which acts on the sensor diaphragm.
  • a rigid mass- less piston (of surface area Sd) supported by a spring (Zd) attached to the transducer housing is a valid approximation for the fixation of the flexible sensor diaphragm onto the transducer housing.
  • the ambient noise picked-up can be split in two 'stages', first the ambient noise pressure signal couples to the transducer housing (via the housing radiation impedance acting as generator output impedance) where it may be transformed to a mechanical force signal and the loading from housing mass as well as attached tissue impedance (e.g. thorax impedance) may be introduced. Then this resulting input force signal undergoes an area transformation, from the inactive housing application area Sh over to the active sensor area Sd, where the loading contributions from the sensor diaphragm (primarily mechanical compliance) and its underlying tissue can be applied.
  • Fig. 3 shows the electrical equivalent circuit of the transmission path from ambient noise via the transducer housing and to the front side of the sensor diaphragm.
  • the sensor output is assumed proportional with the force across the sensor diaphragm compliance element.
  • the resulting force acting on the sensor diaphragm may be calculated using (1). Note the sign inversion on the final impact due to the reaction from the tissue causing a downward force on top of the housing to act upwards on the sensor diaphragm.
  • Zdt denotes contribution from the tissue impedance acting on the sensor diaphragm, a single degree of freedom system (SDOF mass-, compliance- and damping inseries) in dependence of application force and application surface area e.g. as adpted from Vermarien H. and van Vollenhoven E.: "The recording of heart vibrations: a problem of vibration measurement on soft tissue", Medical & Biological Engineering & Computing, 1984, 22, pp 168-178.
  • SDOF mass-, compliance- and damping inseries a single degree of freedom system
  • the housing mass mechanical loading impedance Zhm may be calculated using (4) where Mh is the housing mass.
  • the radiation impedance Zhr may be estimated from (5) which calculates the impedance out into a 2 ⁇ -space, in this equation O h is the equivalent radius of a circular rigid piston of same area as the housing radiation area (e.g. Sh) and k is the
  • the hand/arm impedance loading may be included in series connection with Zhr, Zht and Zhm working within the Sh area domain.
  • the effect on (1) is an added Zha impedance element in the denominator, where
  • the rear side of the sensor diaphragm faces an enclosed volume (room allowing for diaphragm deflection) and the inherent loading of this element will in principle also affect the sensor diaphragm deflection.
  • this enclosed space will act as a soft spring compared to the sensor diaphragm and hence have no practical importance and as a consequence the above equivalent circuit does not contain this element.
  • a representative air-chamber volume compliance impedance element should be inserted in the model in series with Zdt.
  • the usefulness of a transducer for physiological signals depends to a large degree not only on its ability to suppress the influence of noise, but equally on its ability to receive the relevant physiological signals.
  • the input to the transducer occurs via two paths, one being across the thorax impedance, the other being via the housing.
  • the sound source itself is regarded as a high-impedance velocity sound source, and hence the electrical equivalent of the sound transmission for physiological signals may be determined according to the structure shown in Fig. 13, using the nomenclature defined above.
  • the influence from hand/arm holding the transducer housing may be relevant in some situations, and the loading contribution from Zha may then be implemented by applying it in series with Mht and Mh as shown by the x on the drawing. Furthermore an inclusion of an enclosed air-cavity volume is implemented by adding this loading contribution in series with Cd.
  • the force acting on the sensor diaphragm may be calculated from the model in accordance with (7)
  • the performance of a transducer may usefully be expressed as the signal-to-noise (S/N) ratio, and it is frequency dependent.
  • S/N ratio the signal-to-noise ratio
  • the S/N ratio will be given as a function of frequency for some typical configurations.
  • the values in dB are relative only.
  • a transducer of Type I and with the dimensions and weight given above will perform as shown in Fig. 4.
  • the variation has been given in the parameters ah (top) and ad (bottom).
  • Solid lines indicate the nominal value
  • the dashed lines indicate double the nominal respective values
  • the dotted lines indicate half the nominal respective values.
  • Typical auscultation sound information lies below the 1000 Hz limit and by pushing the resonance notch above this point, while maintaining a high level of suppression just beneath it, effectively improves the practical signal-to-noise ratio more, in comparison to tuning the resonance point lower and trying to compensate with even better ambient noise suppression further above the resonance point.
  • the effective variation for the radii are defined as those causing halving, unity or doubling of the area ratio Sd/Sh from its nominal value.
  • the area ratio may be expressed as
  • Typical auscultation sound information lies below the 1000 Hz limit and by pushing the resonance notch above this point, while maintaining a high level of suppression just beneath it, effectively improves the practical signal-to-noise ratio more compared to tuning the resonance point lower and trying to compensate with even better ambient noise suppression further above the resonance point.
  • the concept of opening the transducer housing behind the sensor element has been tried (Type H), thereby allowing for counteracting ambient noise to enter the system.
  • the simplest kind of rear side sound passage is a wide opening, causing the resulting effective pressure on the diaphragm rear side to equal that of the pressure acting on the transducer housing.
  • FIG. 5 shows the physical layout of the simple opened transducer system with the simple opening consisting of a cylindrical conduit having essentially the same diameter as the sensor diaphragm. Thereby the ambient noise is allowed to reach the rear side of the diaphragm without any filtering action.
  • the effect of the simple opening on the total system ambient noise response may be calculated by the according to (9) and (10), which simply subtracts the resulting rear side force component from the complementary frontal side force component as provided above.
  • a transducer of Type II and with the dimensions and weight given above will perform as shown in Fig. 6.
  • the variation has been given in the parameters ah (top) and ad (bottom).
  • Solid lines indicate the nominal value
  • the dashed lines indicate double the nominal respective values
  • the dotted lines indicate half the nominal respective values.
  • This type of transducer may advantageously be provided with acoustic resistance means in the large opening connecting the rear side of the diaphragm to the surrounding air, and preferably flush with the outer surface of the housing.
  • This acoustic resistance means will contribute to an improved S/N ratio in the relatively higher frequency range of the transducer.
  • the means is advantageously chosen from the group comprising felt and non-woven fibrous materials and preferably provided with a water-repellent outer surface. This has the double function of providing not only a well-defined resistive part of the impedance predominantly active in the higher frequency range, but it also provides environmental protection from dust and humidity for the sensitive diaphragm. Furthermore, this type of protection will not change its acoustical properties, even when subjected to dust or water spray in limited quantities.
  • Figures 1 1 and 12 show simulations for the area ratio values 1/20, 1/10 and Vz, realized either through ah variation (Fig. 1 1) or ad variation (Fig. 12). Each graph shows the noise performance for the closed system and furthermore the improvement of the simple opened system over the closed system.
  • the lower set of curves represents the closed transducer system (Type I) response and upper set of curves show the improvement of the simple opened system (Type II) over the closed system.
  • Area ratio Sd/Sh values of 1/20 (dashed), 1/10 (solid) and 1/2 (dotted) have been shown.
  • Fig. 9 shows the physical layout of a transducer system (Type III) having a combined port (an acoustical vent having a resistance and a mass element) and air-cavity volume performing a second order low-pass filtering of the ambient noise before it meets the sensor diaphragm rear side.
  • Fig. 7 shows a Type III transducer in greater detail fitted in a housing. The cavity 7 is in communication with the surrounding air by means of a port 8 with well-defined properties.
  • the surface of the diaphragm touching the skin may be protected by a coat or layer of material 9 that will not influence the pickup by the diaphragm, i.e. it should posses properties similar to the tissue that the diaphragm is touching.
  • the radius ad of the diaphragm is ca. 50% of the radius ah of the housing, corresponding to an area proportion of ca. 25%.
  • the port/volume system is characteristic in its resonance frequency and its overshoot at resonance, below resonance the system is to be considered approximately as a simple opening whereas the response above resonance is a second order low-pass roll-off.
  • the contribution from the sensor diaphragm compliance possibly needs to be included in the modeling.
  • the diaphragm compliance will act in parallel with the air-cavity volume compliance and in cases where the volume compliance is not significantly larger the diaphragm compliance will induce a reduced resonance frequency for the complete system.
  • the equivalent circuit is shown in Fig. 8, which essentially shows the transmission path from the ambient noise floor to the rear side of the sensor diaphragm.
  • Impedance element Zpv is the air-volume acoustic compliance calculated from (13) with V denoting the cavity volume
  • Zpp is the port acoustic impedance, consisting of a damping element and a mass element in series connection, e.g. calculated for a narrow slit which typically is introduced for purposes of elevated damping rates ( 14).
  • the narrow slit impedance may be estimated from its length 1 (parallel to the sound propagation direction), its width a (orthogonal to sound propagation and the least distance between two opposite planes in the slit) and the slit height b the constant ⁇ denotes the air viscosity (approximately 18.3 10 "6 Ns/m).
  • the resulting force acting on the sensor diaphragm in system where the rear side diaphragm pressure signal has passed the port-volume acoustical filter system then becomes the sum of the contribution from each side.
  • a transducer of Type III and with the dimensions and weight given above will perform as shown in Fig. 10.
  • the variation has been given (top to bottom) in ah, ad, mh, and cd, the latter being the compliance of the diaphragm.
  • Solid lines indicate the nominal value
  • the dashed lines indicate double the nominal respective values
  • the dotted lines indicate half the nominal respective values.
  • the acoustic resistance means may usefully be found in the group comprising felt and non-woven fibrous materials, however, they may have to be very compact.
  • the port in the case of Type III when formed as a slit in the housing, may have an appreciable length and a correspondingly narrow width. This has the particular advantage that accidental partial closure will not disturb the function to an appreciable degree.
  • the provision of a non-wettable surface in the slit precludes any trapping of water. In practice, this may be obtained by a PTFE insert with a laser-cut slit.

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  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Molecular Biology (AREA)
  • Public Health (AREA)
  • Medical Informatics (AREA)
  • Biomedical Technology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Multimedia (AREA)
  • Signal Processing (AREA)
  • Details Of Audible-Bandwidth Transducers (AREA)
  • Piezo-Electric Transducers For Audible Bands (AREA)
  • Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)

Abstract

Dans les transducteurs stéthoscopiques électroniques bien connus, l'élément sensible est influencé par les signaux transmis via la peau et le côté arrière est enfermé dans logement pour empêcher les bruits dans l'atmosphère d'atteindre l'élément sensible. Dans cette invention, on obtient un rapport signal/bruit amélioré en laissant le transducteur se comporter comme une membrane de transflexion piézo-électrique en contact avec la peau, le côté arrière de cette membrane étant en communication avec l'air environnant par l'intermédiaire d'un réseau acoustique, de façon à recevoir les bruits dans l'atmosphère, lesquels agissent de façon à contrer l'influence du bruit provenant de la peau.
PCT/DK2003/000427 2002-06-21 2003-06-23 Transducteur pour signaux bioacoustiques WO2004002191A1 (fr)

Priority Applications (6)

Application Number Priority Date Filing Date Title
KR1020047020742A KR100991649B1 (ko) 2002-06-21 2003-06-23 트랜스듀서
JP2004514592A JP4378280B2 (ja) 2002-06-21 2003-06-23 生物音響信号用変換器
US10/518,588 US7593534B2 (en) 2002-06-21 2003-06-23 Transducer for bioacoustic signals
EP03732253A EP1552718B1 (fr) 2002-06-21 2003-06-23 Transducteur pour signaux bioacoustiques
AT03732253T ATE551844T1 (de) 2002-06-21 2003-06-23 Wandler für bioakustische signale
AU2003239776A AU2003239776A1 (en) 2002-06-21 2003-06-23 A transducer for bioacoustic signals

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DKPA200200962 2002-06-21
DKPA200200962 2002-06-21

Publications (1)

Publication Number Publication Date
WO2004002191A1 true WO2004002191A1 (fr) 2003-12-31

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/DK2003/000427 WO2004002191A1 (fr) 2002-06-21 2003-06-23 Transducteur pour signaux bioacoustiques

Country Status (8)

Country Link
US (1) US7593534B2 (fr)
EP (1) EP1552718B1 (fr)
JP (1) JP4378280B2 (fr)
KR (1) KR100991649B1 (fr)
CN (1) CN100556202C (fr)
AT (1) ATE551844T1 (fr)
AU (1) AU2003239776A1 (fr)
WO (1) WO2004002191A1 (fr)

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US7998091B2 (en) 2005-11-23 2011-08-16 3M Innovative Properties Company Weighted bioacoustic sensor and method of using same
US8024974B2 (en) 2005-11-23 2011-09-27 3M Innovative Properties Company Cantilevered bioacoustic sensor and method using same
US8548174B2 (en) 2007-03-23 2013-10-01 3M Innovative Properties Company Modular electronic biosensor with interface for receiving disparate modules
US8594339B2 (en) 2007-03-23 2013-11-26 3M Innovative Properties Company Power management for medical sensing devices employing multiple sensor signal feature detection
EP2928209A1 (fr) 2014-04-02 2015-10-07 MyoDynamik ApS Système permettant d'acquérir des données représentant le son dans un corps humain ou animal
WO2016137798A1 (fr) * 2015-02-23 2016-09-01 The Boston Consulting Group, Inc. Dispositif de surveillance physiologique
WO2019017378A1 (fr) * 2017-07-20 2019-01-24 パイオニア株式会社 Dispositif d'acquisition de sons biologiques
US10610735B2 (en) 2014-12-11 2020-04-07 Curo Diagnostics Aps Assessment of physical fitness of an animal or human individual

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US20080013747A1 (en) * 2006-06-30 2008-01-17 Bao Tran Digital stethoscope and monitoring instrument
JP5182516B2 (ja) * 2006-11-09 2013-04-17 日本電気株式会社 圧電スピーカ及び圧電スピーカを備えた電子機器
US20090030285A1 (en) * 2007-07-25 2009-01-29 Andersen Bjorn K Monitoring of use status and automatic power management in medical devices
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CA2732879A1 (fr) * 2008-08-05 2010-02-11 Guardsman Scientific, Inc. Systeme et procede de gestion d'un patient
US8876720B2 (en) * 2008-08-05 2014-11-04 Guardsman Scientific, Inc. Peripheral ultrasound device providing pivotal adjustment of an imaging mechanism about two axes
CN102475550A (zh) * 2010-11-24 2012-05-30 孙翠玲 振膜直接感振式电子听诊探头
US9462994B2 (en) * 2012-05-11 2016-10-11 3M Innovative Properties Company Bioacoustic sensor with active noise correction
TW201347728A (zh) * 2012-05-17 2013-12-01 Ind Tech Res Inst 生理訊號感測結構及包括所述生理訊號感測結構的聽診器及其製造方法
US8934637B2 (en) * 2012-12-03 2015-01-13 Elegant Medical LLC Electronic stethoscope
USD764064S1 (en) 2013-06-07 2016-08-16 Guardsman Scientific, Inc. Securing mechanism for a peripheral ultrasound device
USD787685S1 (en) 2013-06-07 2017-05-23 Guardsman Scientific, Inc. Probe for a peripheral ultrasound device
USD787684S1 (en) 2013-06-07 2017-05-23 Guardsman Scientific, Inc. Securing mechanism with a probe for a peripheral ultrasound device
WO2015065988A1 (fr) * 2013-10-28 2015-05-07 Smith Clive L Stéthoscope et structure de dispositif électronique
US9530433B2 (en) 2014-03-17 2016-12-27 Sharp Laboratories Of America, Inc. Voice activity detection for noise-canceling bioacoustic sensor
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EP1552718A1 (fr) 2005-07-13
KR100991649B1 (ko) 2010-11-02
US7593534B2 (en) 2009-09-22
AU2003239776A1 (en) 2004-01-06
KR20050010957A (ko) 2005-01-28
ATE551844T1 (de) 2012-04-15
JP4378280B2 (ja) 2009-12-02
EP1552718B1 (fr) 2012-03-28
CN1679372A (zh) 2005-10-05
US20050232434A1 (en) 2005-10-20
JP2005534360A (ja) 2005-11-17
CN100556202C (zh) 2009-10-28

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